Orthopaedic femoral component having controlled condylar curvature

ABSTRACT

An orthopaedic knee prosthesis includes a femoral component having a condyle surface. The condyle surface is defined by one or more radii of curvatures, which are controlled to reduce or delay the onset of anterior translation of the femoral component relative to a tibial bearing.

This application is a continuation of U.S. Utility patent applicationSer. No. 14/453,371 entitled “ORTHOPAEDIC FEMORAL COMPONENT HAVINGCONTROLLED CONDYLAR CURVATURE,” which is a continuation of U.S. Utilitypatent application Ser. No. 12/165,579, now U.S. Pat. No. 8,828,086entitled “ORTHOPAEDIC FEMORAL COMPONENT HAVING CONTROLLED CONDYLARCURVATURE,” both of which are expressly incorporated herein byreference.

CROSS-REFERENCE TO RELATED U.S. PATENT APPLICATION

Cross-reference is made to U.S. Utility patent application Ser. No.12/165,574 entitled “Posterior Cruciate-Retaining Orthopaedic KneeProsthesis Having Controlled Condylar Curvature” by Christel M. Wagner,which was filed on Jun. 30, 2008; to U.S. Utility patent applicationSer. No. 12/165,575 entitled “Posterior Stabilized Orthopaedic KneeProsthesis Having Controlled Condylar Curvature” by Joseph G. Wyss,which was filed on Jun. 30, 2008; and to U.S. Utility patent applicationSer. No. 12/165,582 entitled “Posterior Stabilized OrthopaedicProsthesis” by Joseph G. Wyss, which was filed on Jun. 30, 2008; and toU.S. Utility patent application Ser. No. 12/488,107 entitled“Orthopaedic Knee Prosthesis Having Controlled Condylar Curvature” byMark A. Heldreth, which was filed on Jun. 19, 2009; the entirety of eachof which is incorporated herein by reference.

TECHNICAL FIELD

The present disclosure relates generally to orthopaedic prostheses, andparticularly to orthopaedic prostheses for use in knee replacementsurgery.

BACKGROUND

Joint arthroplasty is a well-known surgical procedure by which adiseased and/or damaged natural joint is replaced by a prosthetic joint.A typical knee prosthesis includes a tibial tray, a femoral component,and a polymer insert or bearing positioned between the tibial tray andthe femoral component. Depending on the severity of the damage to thepatient's joint, orthopaedic prostheses of varying mobility may be used.For example, the knee prosthesis may include a “fixed” tibial bearing incases wherein it is desirable to limit the movement of the kneeprosthesis, such as when significant soft tissue damage or loss ispresent. Alternatively, the knee prosthesis may include a “mobile”tibial bearing in cases wherein a greater degree of freedom of movementis desired. Additionally, the knee prosthesis may be a total kneeprosthesis designed to replace the femoral-tibial interface of bothcondyles of the patient's femur or a uni-compartmental (or uni-condylar)knee prosthesis designed to replace the femoral-tibial interface of asingle condyle of the patient's femur.

The type of orthopedic knee prosthesis used to replace a patient'snatural knee may also depend on whether the patient's posterior cruciateligament is retained or sacrificed (i.e., removed) during surgery. Forexample, if the patient's posterior cruciate ligament is damaged,diseased, and/or otherwise removed during surgery, a posteriorstabilized knee prosthesis may be used to provide additional supportand/or control at later degrees of flexion. Alternatively, if theposterior cruciate ligament is intact, a cruciate retaining kneeprosthesis may be used.

Typical orthopaedic knee prostheses are generally designed to duplicatethe natural movement of the patient's joint. As the knee is flexed andextended, the femoral and tibial components articulate and undergocombinations of relative anterior-posterior motion and relativeinternal-external rotation. However, the patient's surrounding softtissue also impacts the kinematics and stability of the orthopaedic kneeprosthesis throughout the joint's range of motion. That is, forcesexerted on the orthopaedic components by the patient's soft tissue maycause unwanted or undesirable motion of the orthopaedic knee prosthesis.For example, the orthopaedic knee prosthesis may exhibit an amount ofunnatural (paradoxical) anterior translation as the femoral component ismoved through the range of flexion.

In a typical orthopaedic knee prosthesis, paradoxical anteriortranslation may occur at nearly any degree of flexion, but particularlyat mid to late degrees of flexion. Paradoxical anterior translation canbe generally defined as an abnormal relative movement of a femoralcomponent on a tibial bearing wherein the contact “point” between thefemoral component and the tibial bearing “slides” anteriorly withrespect to the tibial bearing. This paradoxical anterior translation mayresult in loss of joint stability, accelerated wear, abnormal kneekinematics, and/or cause the patient to experience a sensation ofinstability during some activities.

SUMMARY

According to one aspect, an orthopaedic knee prosthesis may include afemoral component and a tibial bearing. The femoral component mayinclude a condyle surface that is curved in the sagittal plane. Thetibial bearing may include a bearing surface configured to articulatewith the condyle surface of the femoral component. In some embodiments,the condyle surface of the femoral component may contact the bearingsurface at a first contact point on the condyle surface at a firstdegree of flexion equal to about 0 degrees. The condyle surface may alsocontact the bearing surface at a second contact point on the condylesurface at a second degree of flexion. The second degree of flexion maybe greater than the first degree of flexion. For example, the seconddegree of flexion may be in the range of about 10 degrees to about 100degrees. In one particular embodiment, the second degree of flexion isabout 30 degrees.

The condyle surface in the sagittal plane may have a first radius ofcurvature at the first contact point and a second radius of curvature atthe second contact point. The second radius of curvature may be greaterthan the first radius of curvature by at least 0.5 millimeters. Forexample, the second radius may greater than the first radius by adistance of at least 2 millimeters or by at least 5 millimeters. in someembodiments, the ratio of the first radius of curvature to the secondradius of curvature is in the range of 0.50 to 0.99. For example, theratio of the first radius of curvature to the second radius of curvaturemay be in the range of 0.90 to 0.99.

Additionally, in some embodiments, the condyle surface may contact thebearing surface at a third contact point on the condyle surface at athird degree of flexion. The third degree of flexion may be greater thanthe second degree of flexion and less than about 90 degrees. The condylesurface in the sagittal plane may have a third radius of curvature atthe third contact point. The third radius of curvature may be greaterthan the first radius of curvature and less than the second radius ofcurvature. For example, in some embodiments, the third radius is greaterthan the second radius by at least 0.5 millimeters. However, in otherembodiments, the third radius of curvature may be greater than the firstand second radii of curvature.

In some embodiments, the condyle surface of the femoral component is amedial condyle surface and the bearing surface of the tibial bearing isa medial bearing surface. The femoral component may include a lateralcondyle surface curved in the sagittal plane. The tibial bearing mayinclude a lateral bearing surface configured to articulate with thelateral condyle surface of the femoral component. In some embodiments,the lateral condyle surface and the medial condyle surface aresubstantially symmetrical in the sagittal plane. However, in otherembodiments, the lateral condyle surface and the medial condyle surfaceare not substantially symmetrical in the sagittal plane.

Additionally, in some embodiments, the lateral condyle surface maycontact the lateral bearing surface at a first point on the lateralcondyle surface at a third degree of flexion. The third degree offlexion may be less than about 30 degrees. The lateral condyle surfacemay also contact the lateral bearing surface at a second point on thelateral condyle surface at a fourth degree of flexion. The fourth degreeof flexion may be greater than the third degree of flexion.Additionally, the lateral condyle surface in the sagittal plane mayinclude a first radius of curvature at the first contact point and asecond radius of curvature at the second contact point. The secondradius of curvature may be greater than the first radius of curvature byat least 0.5 millimeters. In some embodiments, the second radius ofcurvature of the lateral condyle may be different from the second radiusof curvature of the medial condyle. Additionally, in some embodiments,the second degree of flexion may be different from the fourth degree offlexion. Further, in some embodiments, the difference between the firstradius of curvature and the second radius of curvature is different fromthe difference between the third radius of curvature and the fourthradius of curvature.

According to another aspect, and orthopaedic knee prosthesis may includea femoral component and a tibial bearing. The femoral component mayinclude a condyle surface curved in the sagittal plane. The tibialbearing may include a bearing surface configured to articulate with thecondyle surface of the femoral component. The condyle surface maycontact the bearing surface at a first contact point on the condylesurface at a first degree of flexion. The first degree of flexion may beless than 30 degrees. The condyle surface may also contact the bearingsurface at a second contact point on the condyle surface at a seconddegree of flexion. The second degree of flexion may be greater thanabout 30 degrees.

In such embodiments, the condyle surface in the sagittal plane has afirst radius of curvature at the first contact point and a second radiusof curvature at the second contact point. The ratio of the first radiusof curvature to the second radius of curvature may be in the range of0.80 to 0.99. For example, the ratio of the first radius of curvature tothe second radius of curvature may be in the range of 0.90 to 0.99.

According to a further aspect, an orthopaedic knee prosthesis mayinclude a femoral component and a tibial bearing. The femoral componentmay include a condyle surface curved in the sagittal plane. The tibialbearing may include a bearing surface configured to articulate with thecondyle surface of the femoral component. The condyle surface maycontact the bearing surface at a first contact point on the condylesurface at a first degree of flexion. The first degree of flexion maybe, for example, about 0 degrees. The condyle surface may also contactthe bearing surface at a second contact point on the condyle surface ata second degree of flexion. The second degree of flexion may be greaterthan about 50 degrees. For example, in some embodiments, the seconddegree of flexion may be greater than about 70 degrees.

In some embodiments, the condyle surface in the sagittal plane mayinclude a curved surface section extending from the first contact pointto the second contact point. The curved surface section may be definedby a substantially constant radius of curvature.

According to yet another aspect, an orthopaedic knee prosthesis mayinclude a femoral component. The femoral component may include a condylesurface curved in the sagittal plane. The condyle surface may include ananterior surface and a posterior surface. The anterior surface and theposterior surface may meet at an inferior-most point on the condylesurface. The posterior surface may include a superior-most point and amid-point located equidistance from the superior-most point and theinferior-most point. The posterior surface in the sagittal plane mayhave a first radius of curvature at a first point on the posteriorsurface between the inferior-most point and the mid-point. The posteriorsurface in the sagittal plane may have a second radius of curvature at asecond point on the posterior surface between the first point and thesuperior-most point. The second radius of curvature may be greater thanthe first radius of curvature by at least 0.5 millimeters.

BRIEF DESCRIPTION OF THE DRAWINGS

The detailed description particularly refers to the following figures,in which:

FIG. 1 is an exploded perspective view of one embodiment of anorthopaedic knee prosthesis;

FIG. 2 is an exploded perspective view of another embodiment of anorthopaedic knee prosthesis;

FIG. 3 is a cross-section view of one embodiment of a femoral componentand tibial bearing of FIG. 1 taken generally along section lines 2-2 andhaving the femoral component articulated to a first degree of flexion;

FIG. 4 is a cross-sectional view of a femoral component and tibialbearing of FIG. 3 having the femoral component articulated to a seconddegree of flexion;

FIG. 5 is a cross-sectional view of a femoral component and tibialbearing of FIG. 3 having the femoral component articulated to a thirddegree of flexion;

FIG. 6 is a cross-sectional view of one embodiment of the femoralcomponent of FIG. 1;

FIG. 7 is a cross-sectional view of another embodiment of the femoralcomponent of FIG. 1;

FIG. 8 is a cross-sectional view of another embodiment of the femoralcomponent of FIG. 1;

FIG. 9 is a cross-sectional view of another embodiment of the femoralcomponent of FIG. 1;

FIG. 10 is a graph of the anterior-posterior translation of a simulatedfemoral component having an increased radius of curvature located atvarious degrees of flexion;

FIG. 11 is a graph of the internal rotation (as indicated by an upwardor positive direction in the graph) of a simulated tibial insert withrespect to the simulated femoral component of FIG. 10;

FIG. 12 is a graph of the anterior-posterior translation of anothersimulated femoral component having an increased radius of curvaturelocated at various degrees of flexion;

FIG. 13 is a graph of the internal rotation (as indicated by an upwardor positive direction in the graph) of a simulated tibial insert withrespect to the simulated femoral component of FIG. 12;

FIG. 14 is a graph of the anterior-posterior translation of anothersimulated femoral component having an increased radius of curvaturelocated at various degrees of flexion;

FIG. 15 is a graph of the internal rotation (as indicated by an upwardor positive direction in the graph) of a simulated tibial insert withrespect to the simulated femoral component of FIG. 14;

FIG. 16 is a graph of the anterior-posterior translation of anothersimulated femoral component having an increased radius of curvaturelocated at various degrees of flexion;

FIG. 17 is a graph of the internal rotation (as indicated by an upwardor positive direction in the graph) of a simulated tibial insert withrespect to the simulated femoral component of FIG. 16;

FIG. 18 is a cross-sectional view of another embodiment of the femoralcomponent of FIG. 1;

FIG. 19 is a cross-sectional view of another embodiment of the femoralcomponent of FIG. 1;

FIG. 20 is a cross-sectional view of another embodiment of the femoralcomponent of FIG. 1; and

FIG. 21 is a cross-sectional view of another condyle of anotherembodiment of the femoral component of FIG. 1.

DETAILED DESCRIPTION OF THE DRAWINGS

While the concepts of the present disclosure are susceptible to variousmodifications and alternative forms, specific exemplary embodimentsthereof have been shown by way of example in the drawings and willherein be described in detail. It should be understood, however, thatthere is no intent to limit the concepts of the present disclosure tothe particular forms disclosed, but on the contrary, the intention is tocover all modifications, equivalents, and alternatives falling withinthe spirit and scope of the invention as defined by the appended claims.

Terms representing anatomical references, such as anterior, posterior,medial, lateral, superior, inferior, etcetera, may be used throughoutthis disclosure in reference to both the orthopaedic implants describedherein and a patient's natural anatomy. Such terms have well-understoodmeanings in both the study of anatomy and the field of orthopaedics. Useof such anatomical reference terms in the specification and claims isintended to be consistent with their well-understood meanings unlessnoted otherwise.

Referring now to FIG. 1, in one embodiment, an orthopaedic kneeprosthesis 10 includes a femoral component 12, a tibial bearing 14, anda tibial tray 16. The femoral component 12 and the tibial tray 16 areillustratively formed from a metallic material such as cobalt-chromiumor titanium, but may be formed from other materials, such as a ceramicmaterial, a polymer material, a bio-engineered material, or the like, inother embodiments. The tibial bearing 14 is illustratively formed from apolymer material such as a ultra-high molecular weight polyethylene(UHMWPE), but may be formed from other materials, such as a ceramicmaterial, a metallic material, a bio-engineered material, or the like,in other embodiments.

As discussed in more detail below, the femoral component 12 isconfigured to articulate with the tibial bearing 14, which is configuredto be coupled with the tibial tray 16. In the illustrative embodiment ofFIG. 1, the tibial bearing 14 is embodied as a rotating or mobile tibialbearing and is configured to rotate relative to the tibial tray 12during use. However, in other embodiments, the tibial bearing 14 may beembodied as a fixed tibial bearing, which may be limited or restrictedfrom rotating relative the tibial tray 16.

The tibial tray 16 is configured to be secured to a surgically-preparedproximal end of a patient's tibia (not shown). The tibial tray 16 may besecured to the patient's tibia via use of bone adhesive or otherattachment means. The tibial tray 16 includes a platform 18 having a topsurface 20 and a bottom surface 22. Illustratively, the top surface 20is generally planar and, in some embodiments, may be highly polished.The tibial tray 16 also includes a stem 24 extending downwardly from thebottom surface 22 of the platform 18. A cavity or bore 26 is defined inthe top surface 20 of the platform 18 and extends downwardly into thestem 24. The bore 26 is formed to receive a complimentary stem of thetibial insert 14 as discussed in more detail below.

As discussed above, the tibial bearing 14 is configured to be coupledwith the tibial tray 16. The tibial bearing 14 includes a platform 30having an upper bearing surface 32 and a bottom surface 34. In theillustrative embodiment wherein the tibial bearing 14 is embodied as arotating or mobile tibial bearing, the bearing 14 includes a stem 36extending downwardly from the bottom surface 32 of the platform 30. Whenthe tibial bearing 14 is coupled to the tibial tray 16, the stem 36 isreceived in the bore 26 of the tibial tray 16. In use, the tibialbearing 14 is configured to rotate about an axis defined by the stem 36relative to the tibial tray 16. In embodiments wherein the tibialbearing 14 is embodied as a fixed tibial bearing, the bearing 14 may ormay not include the stem 22 and/or may include other devices or featuresto secure the tibial bearing 14 to the tibial tray 12 in a non-rotatingconfiguration.

The upper bearing surface 32 of the tibial bearing 14 includes a medialbearing surface 42 and a lateral bearing surface 44. The medial andlateral bearing surfaces 42, 44 are configured to receive or otherwisecontact corresponding medial and lateral condyles of the femoralcomponent 14 as discussed in more detail below. As such, each of thebearing surface 42, 44 has a concave contour.

The femoral component 12 is configured to be coupled to asurgically-prepared surface of the distal end of a patient's femur (notshown). The femoral component 12 may be secured to the patient's femurvia use of bone adhesive or other attachment means. The femoralcomponent 12 includes an outer, articulating surface 50 having a pair ofmedial and lateral condyles 52, 54. The condyles 52, 54 are spaced apartto define an intracondyle opening 56 therebetween. In use, the condyles52, 54 replace the natural condyles of the patient's femur and areconfigured to articulate on the corresponding bearing surfaces 42, 44 ofthe platform 30 of the tibial bearing 14.

The illustrative orthopaedic knee prosthesis 10 of FIG. 1 is embodied asa posterior cruciate-retaining knee prosthesis. That is, the femoralcomponent 12 is embodied as a posterior cruciate-retaining kneeprosthesis and the tibial bearing 14 is embodied as a posteriorcruciate-retaining tibial bearing 14. However, in other embodiments, theorthopaedic knee prosthesis 10 may be embodied as a posteriorcruciate-sacrificing knee prosthesis as illustrated in FIG. 2.

In such embodiments, the tibial bearing 14 is embodied as posteriorstabilizing tibial bearing and includes a spine 60 extending upwardlyfrom the platform 30. The spine 60 is positioned between the bearingsurfaces 42, 44 and includes an anterior side 62 and a posterior side 64having a cam surface 66. In the illustrative embodiment, the cam surface66 has a substantially concave curvature. However, spines 60 includingcam surfaces 66 having other geometries may be used in otherembodiments. For example, a tibial bearing including a spine having asubstantially “S”-shaped cross-sectional profile, such as the tibialbearing described in U.S. patent application Ser. No. 12/165,582,entitled “Posterior Stabilized Orthopaedic Prosthesis” by Joseph G.Wyss, et al., which is hereby incorporated by reference, may be used inother embodiments.

Additionally, in such embodiments, the femoral component 12 is embodiedas a posterior stabilized femoral component and includes an intracondylenotch or recess 57 (rather than an opening 56). A posterior cam 80(shown in phantom) and an anterior cam 82 are positioned in theintracondyle notch 57. The posterior cam 80 is located toward theposterior side of the femoral component 12 and includes a cam surface 86configured to engage or otherwise contact the cam surface 66 of thespine 60 of the tibial bearing 12 during.

It should be appreciated that although the orthopaedic knee prosthesis10 may be embodied as either a posterior cruciate-retaining orcruciate-sacrificing knee prosthesis, the femoral component 12 and thetibial bearing 14 of the knee prosthesis 10 are discussed below, andillustrated in the remaining figures, in regard to a posteriorcruciate-retaining knee prosthesis with the understanding that suchdescription is equally applicable to those embodiments whereinorthopaedic knee prosthesis 10 is embodied as a posteriorcruciate-sacrificing (posterior stabilized) orthopaedic knee prosthesis.

It should be appreciated that the illustrative orthopaedic kneeprosthesis 10 is configured to replace a patient's right knee and, assuch, the bearing surface 42 and the condyle 52 are referred to as beingmedially located; and the bearing surface 44 and the condyle 54 arereferred to as being laterally located. However, in other embodiments,the orthopaedic knee prosthesis 10 may be configured to replace apatient's left knee. In such embodiments, it should be appreciated thatthe bearing surface 42 and the condyle 52 may be laterally located andthe bearing surface 44 and the condyle 54 may be medially located.Regardless, the features and concepts described herein may beincorporated in an orthopaedic knee prosthesis configured to replaceeither knee joint of a patient.

Referring now to FIGS. 3-5, the femoral component 12 is configured toarticulate on the tibial bearing 14 during use. Each condyle 52, 54 ofthe femoral component 12 includes a condyle surface 100, which isconvexly curved in the sagittal plane and configured to contact therespective bearing surface 42, 44. For example, in one embodiment asshown in FIG. 3, when the orthopaedic knee prosthesis 10 is in extensionor is otherwise not in flexion (e.g., a flexion of about 0 degrees), thecondyle surface 100 of the condyle 52 contacts the bearing surface 42(or bearing surface 44 in regard to condyle 54) at one or more contactpoints 102 on the condyle surface 100.

Additionally, as the orthopaedic knee prosthesis 10 is articulatedthrough the middle degrees of flexion, the femoral component 12 contactsthe tibial bearing 14 at one or more contact points on the condylesurface 100. For example, in one embodiment as illustrated in FIG. 4,when the orthopaedic knee prosthesis 10 is articulated to a middledegree of flexion (e.g., at about 45 degrees), the condyle surface 100contacts the bearing surface 42 at one or more contact points 104 on thecondyle surface 100. Similarly, as the orthopaedic knee prosthesis 10 isarticulated to a late degree of flexion (e.g., at about 70 degrees offlexion), the condyle surface 100 contacts the bearing surface 42 at oneor more contact points 106 on the condyle surface 100 as illustrated inFIG. 5. It should be appreciated, of course, that the femoral component12 may contact the tibial bearing 14 at a plurality of contact points onthe condyle surface 100 at any one particular degree of flexion.However, for clarity of description, only the contact points 102, 104,106 have been illustrated in FIGS. 3-5, respectively.

The orthopaedic knee prosthesis 10 is configured such that the amount ofparadoxical anterior translation of the femoral component 12 relative tothe tibial bearing 14 may be reduced or otherwise delayed to a later(i.e., larger) degree of flexion. In particular, as discussed in moredetail below, the condyle surface 100 of one or both of the condyles 52,54 has particular geometry or curvature configured to reduce and/ordelay anterior translations and, in some embodiments, promote“roll-back” or posterior translation, of the femoral component 12. Itshould be appreciated that by delaying the onset of paradoxical anteriortranslation of the femoral component 12 to a larger degree of flexion,the overall occurrence of paradoxical anterior translation may bereduced during those activities of a patient in which deep flexion isnot typically obtained.

In a typical orthopaedic knee prosthesis, paradoxical anteriortranslation may occur whenever the knee prosthesis is positioned at adegree of flexion greater than zero degrees. The likelihood of anteriortranslation generally increases as the orthopaedic knee prosthesis isarticulated to larger degrees of flexion, particularly in themid-flexion range. In such orientations, paradoxical anteriortranslation of the femoral component on the tibial bearing can occurwhenever the tangential (traction) force between the femoral componentand the tibial bearing fails to satisfy the following equation:

T<μN  (1)

wherein “T” is the tangential (traction) force, “μ” is the coefficientof friction of the femoral component and the tibial bearing, and “N” isthe normal force between the femoral component and the tibial bearing.As a generalization, the tangential (traction) force between the femoralcomponent and the tibial bearing can be defined as

T=M/R  (2)

wherein “T” is the tangential (traction) force between the femoralcomponent and the tibial bearing, “M” is the knee moment, and “R” is theradius of curvature in the sagittal plane of the condyle surface incontact with the tibial bearing at the particular degree of flexion. Itshould be appreciated that equation (2) is a simplification of thegoverning real-world equations, which does not consider such otherfactors as inertia and acceleration. Regardless, the equation (2)provides insight that paradoxical anterior translation of an orthopaedicknee prosthesis may be reduced or delayed by controlling the radius ofcurvature of the condyle surface of the femoral component. That is, bycontrolling the radius of curvature of the condyle surface (e.g.,increasing or maintaining the radius of curvature), the right-hand sideof equation (2) may be reduced, thereby decreasing the value of thetangential (traction) force and satisfying the equation (1). Asdiscussed above, by ensuring that the tangential (traction) forcesatisfies equation (1), paradoxical anterior translation of the femoralcomponent on the tibial bearing may be reduced or otherwise delayed to agreater degree of flexion.

Based on the above analysis, to reduce or delay the onset of paradoxicalanterior translation, the geometry of the condyle surface 100 of one orboth of the condyles 52, 54 of the femoral component 12 is controlled.For example, in some embodiments, the radius of curvature of the condylesurface 100 is controlled such that the radius of curvature is heldconstant over a range of degrees of flexion and/or is increased in theearly to mid flexion ranges. Comparatively, typical femoral componentshave decreasing radii of curvatures beginning at the distal radius ofcurvature (i.e., at about 0 degrees of flexion). However, it has beendetermined that by maintaining a relatively constant radius of curvature(i.e., not decreasing the radius of curvature) over a predeterminedrange of degrees of early to mid-flexion and/or increasing the radius ofcurvature over the predetermined range of degrees of flexion may reduceor delay paradoxical anterior translation of the femoral component 12.Additionally, in some embodiments, the rate of change in the radius ofcurvature of the condyle surface in the early to mid flexion ranges(e.g., from about 0 degrees to about 90 degrees) is controlled such thatthe rate of change is less than a predetermined threshold. That is, ithas been determined that if the rate of decrease of the radius ofcurvature of the condyle surface 100 is greater than the predeterminedthreshold, paradoxical anterior translation may occur.

Accordingly, in some embodiments as illustrated in FIGS. 6-8, thecondyle surface 100 of the femoral component 12 has an increased radiusof curvature in early to middle degrees of flexion from a smaller radiusof curvature R1 to a larger radius of curvature R2. By increasing theradius of curvature, paradoxical anterior translation may be reduced ordelayed to a later degree of flexion as discussed in more detail below.

The amount of increase between the radius of curvature R2 and the radiusof curvature R3, as well as, the degree of flexion on the condylesurface 100 at which such increase occurs has been determined to affectthe occurrence of paradoxical anterior translation. Multiple simulationsof various femoral component designs were performed using theLifeMOD/Knee Sim, version 1007.1.0 Beta 16 software program, which iscommercially available from LifeModeler, Inc. of San Clemente, Calif.,to analyze the effect of increasing the radius of curvature of thecondyle surface of the femoral components in early and mid flexion.Based on such analysis, it has been determined that paradoxical anteriortranslation of the femoral component relative to the tibial bearing maybe reduced or otherwise delayed by increasing the radius of curvature ofthe condyle surface by an amount in the range of about 0.5 millimetersto about 5 millimeters or more at a degree of flexion in the range ofabout 30 degrees of flexion to about 90 degrees of flexion.

For example, the graphs 200, 250 illustrated in FIGS. 10 and 11 presentthe results of a deep bending knee simulation using a femoral componentwherein the radius of curvature of the condyle surface is increased by0.5 millimeters (i.e., from 25.0 millimeters to 25.5 millimeters) at 30degrees of flexion, at 50 degrees of flexion, at 70 degrees of flexion,and at 90 degrees of flexion. Similarly, the graphs 300, 350 illustratedin FIGS. 12 and 13 present the results of a deep bending knee simulationusing a femoral component wherein the radius of curvature of the condylesurface is increased by 1.0 millimeters (i.e., from 25.0 millimeters to26.0 millimeters) at 30 degrees of flexion, at 50 degrees of flexion, at70 degrees of flexion, and at 90 degrees of flexion. The graphs 400 and450 illustrated in FIGS. 14 and 15 present the results of a deep bendingknee simulation using a femoral component wherein the radius ofcurvature of the condyle surface is increased by 2.0 millimeters (i.e.,from 25.0 millimeters to 27.0 millimeters) at 30 degrees of flexion, at50 degrees of flexion, at 70 degrees of flexion, and at 90 degrees offlexion. Additionally, the graphs 500, 550 illustrated in FIGS. 16 and17 present the results of a deep bending knee simulation using a femoralcomponent wherein the radius of curvature of the condyle surface isincreased by 5.0 millimeters (i.e., from 25.0 millimeters to 26.0millimeters) at 30 degrees of flexion, at 50 degrees of flexion, at 70degrees of flexion, and at 90 degrees of flexion.

In the graphs 200, 300, 400, 500, the condylar lowest or most distalpoints (CLP) of the medial condyle (“med”) and the lateral condyle(“lat”) of the femoral component are graphed as a representation of therelative positioning of the femoral component to the tibial bearing. Assuch, a downwardly sloped line represents roll-back of the femoralcomponent on the tibial bearing and an upwardly sloped line representsanterior translation of the femoral component on the tibial bearing. Inthe graphs 250, 350, 450, 550, the amount of relative internal-externalrotation in degrees between the simulated femoral component and tibialbearing for each illustrative embodiment are graphed with respect toeach degree of flexion. An upwardly sloped line in graphs 250, 350, 450,550 corresponds to an amount of internal rotation of the tibia withrespect to the femur (or external rotation of the femur with respect tothe tibia).

As illustrated in the graphs 200, 300, 400, 500, anterior sliding of thefemoral component was delayed until after about 100 degrees of flexionin each of the embodiments; and the amount of anterior translation waslimited to less than about 1 millimeter. In particular, “roll-back” ofthe femoral component on the tibial bearing was promoted by largerincreases in the radius of curvature of the condyle surface at earlierdegrees of flexion. Additionally, as illustrated in graphs 250, 350,450, 550, internal-external rotation between the femoral component andtibial bearing was increased by larger increases in the radius ofcurvature of the condyle surface at earlier degrees of flexion. Ofcourse, amount of increase in the radius of curvature and the degree offlexion at which such increase is introduced is limited by other factorssuch as the anatomical joint space of the patient's knee, the size ofthe tibial bearing, and the like. Regardless, based on the simulationsreported in the graphs 200, 250, 300, 350, 400, 450, 500, 550,paradoxical anterior translation of the femoral component on the tibialbearing can be reduced or otherwise delayed by increasing the radius ofcurvature of the condyle surface of the femoral component during earlyto mid flexion.

Accordingly, referring back to FIGS. 6-9, the condyle surface 100 in thesagittal plane is formed in part from a number of curved surfacesections 102, 104 in one embodiment. The sagittal ends of each curvedsurface section 102, 204 are tangent to the sagittal ends of anyadjacent curved surface section of the condyles surface 100. Each curvedsurface section 102, 104 is defined by a respective radius of curvature.In particular, the curved surface section 102 is defined by a radius ofcurvature R1 and the curved surface section 104 is defined by a radiusof curvature R2.

As discussed above, the condyle surface 100 of the femoral component 12is configured such that the radius of curvature R2 of the curved surfacesection 104 is greater than the radius of curvature R1 of the curvedsurface section 102. In one embodiment, the radius of curvature R2 isgreater than the radius of curvature R1 by 0.5 millimeters or more. Inanother embodiment, the radius of curvature R2 is greater than theradius of curvature R1 by 1 millimeters or more. Additionally in anotherembodiment, the radius of curvature R2 is greater than the radius ofcurvature R1 by 2 millimeters or more. In a particular embodiment, theradius of curvature R2 is greater than the radius of curvature R3 by adistance in the range of about 0.5 millimeters to about 5 millimeters.

It should be appreciated, however, that the particular increase ofradius of curvature between R1 and R2 may be based on or scaled to theparticular size of the femoral component 12 in some embodiments. Forexample, in some embodiments, the increase of the radius of curvaturebetween R1 and R2 may be based on the size of R1. That is, the ratio ofthe radius of curvature R1 to the radius of curvature R2 may be below apredetermined threshold or within a specified range of a target value insome embodiments. For example, in some embodiments, the ratio of theradius of curvature R1 to the radius of curvature R2 is between 0.80 and0.99. In one particular embodiment, the ratio of the radius of curvatureR1 to the radius of curvature R2 is between 0.90 and 0.99.

Each of the curved surface sections 102, 104 contacts the bearingsurface 42 (or 44) of the tibial bearing 14 through different ranges ofdegrees of flexion. For example, the curved surface section 102 extendsfrom an earlier degree of flexion θ1 to a later degree of flexion θ2.The curved surface section 104 extends from the degree of flexion θ2 toa later degree of flexion θ3. The particular degrees of flexion θ1, θ2,and θ3, may vary between embodiments and be based on criteria such asthe type of orthopaedic prosthesis (e.g., cruciate retaining orposterior stabilized), positioning of other component of the orthopaedicprosthesis (e.g., the positioning of a cam of the femoral component 12),the size of the femoral cam, the curvature of the tibial bearing 14, theanatomy of a patient, etc. For example, in one embodiment, asillustrated in FIG. 6, the curved surface section 102 extends from adegree of flexion θ1 of about 0 degrees of flexion to a degree offlexion θ2 of about 30 degrees of flexion. The curved surface section104 extends from the degree of flexion θ2 of about 30 degrees of flexionto a degree of flexion θ3 of about 110 degrees of flexion.

As discussed above, the particular degrees of flexion θ1, θ2, θ3 may bedetermined based on the particular embodiment and other features of thefemoral component 12. For example, the larger degree of flexion θ3 maybe determined or otherwise based on the desire to allow the mostposterior-superior end 110 of the femoral component 12 to “wrap” around.Such a configuration may properly size or configure the femoralcomponent 12 for positioning within the joint gap of a patient. The end110 of the femoral component 12 may be formed from a number ofadditional radii of curvatures, which begin at the degree of flexion θ3.As such, the particular degree of flexion θ3 may be determined or basedon the degree of flexion at which the additional radii of curvaturesmust begin to form the end 110 as desired.

In another embodiment, as illustrated in FIG. 7, the curved surfacesection 102 extends from a degree of flexion θ1 of about 0 degrees offlexion to a degree of flexion θ2 of about 50 degrees of flexion. Thecurved surface section 104 extends from the degree of flexion θ2 ofabout 50 degrees of flexion to a degree of flexion θ3 of about 110degrees of flexion. Additionally, in another embodiment, as illustratedin FIG. 8, the curved surface section 102 extends from a degree offlexion θ1 of about 0 degrees of flexion to a degree of flexion θ2 ofabout 70 degrees of flexion. The curved surface section 104 extends fromthe degree of flexion θ2 of about 70 degrees of flexion to a degree offlexion θ3 of about 110 degrees of flexion. In another illustrativeembodiment, as illustrated in FIG. 9, the curved surface section 102extends from a degree of flexion θ1 of about 0 degrees of flexion to adegree of flexion θ2 of about 90 degrees of flexion. The curved surfacesection 104 extends from the degree of flexion θ2 of about 90 degrees offlexion to a degree of flexion θ3 of about 110 degrees of flexion.

Again, it should be appreciated that the embodiments of FIGS. 6-9 areillustrative embodiments and, in other embodiments, each of the curvedsurface sections 102, 104 may extend from degrees of flexion differentfrom those shown and discussed above in regard to FIGS. 6-9. Forexample, in each of the embodiments of FIGS. 6-9, although the curvedsurface section 102 is illustrated as beginning at about 0 degrees offlexion, the curved surface section 102 may begin at a degree of flexionprior to 0 degrees of flexion (i.e., a degree of hyperextension) inother embodiments.

Referring now to FIG. 18, it should be appreciated that although theillustrative embodiments of FIGS. 6-9 include only one increase ofradius of curvature (i.e., between R1 and R2), the condyle surface mayinclude any number of increases in radius of curvature in otherembodiments. For example, in one embodiment as shown in FIG. 18, thecondyle surface 100 may be formed from a number of curved surfacesections 600, 602, 604, 606, 608, the sagittal ends of each of which aretangent to adjacent curved surface sections. The curved surface section600 extends from an earlier degree of flexion θ1 to a later degree offlexion θ2. The curved surface section 602 extends from the degree offlexion θ2 to a later degree of flexion θ3. The curved surface section604 extends from the degree of flexion θ3 to a later degree of flexionθ4. The curved surface section 606 extends from the degree of flexion θ4to a later degree of flexion θ5. The curved surface section 608 extendsfrom the degree of flexion θ5 to a later degree of flexion θ6.

Each of the curved surface sections 600, 602, 604, 606, 608 is definedby a respective radius of curvature. In particular, the curved surfacesection 600 is defined by a radius of curvature R1, the curved surfacesection 602 is defined by a radius of curvature R2, the curved surfacesection 604 is defined by a radius of curvature R3, the curved surfacesection 606 is defined by a radius of curvature R4, and the curvedsurface section 607 is defined by a radius of curvature R5. The radiusof curvature R2 is greater than the radius of curvature R1. Similarly,the radius of curvature R3 is greater than the radius of curvature R2.The radius of curvature R4 is greater than the radius of curvature R3.And, the radius of curvature R5 is greater than the radius of curvatureR4. In this way, the condyle surface 100 is formed from a plurality ofcurved surface sections, each having a radius of curvature greater thanthe adjacent anterior curved surface section. Again, the embodimentillustrated in FIG. 18 is just one illustrative embodiment. In otherembodiments, the condyle surface 100 may be formed from a greater orlesser number of curved surface sections having an increased radius ofcurvature relative to an anteriorly adjacent curved surface section.

Referring now to FIG. 19, the condyle surface 100 may include anincrease in radius of curvature and a decrease in radius of curvature inthe early to middle degrees of flexion. That is, in some embodiments,the radius of curvature of the condyle surface 100 may initiallyincrease from an initial radius of curvature to an increased radius ofcurvature and subsequently decrease to a decreased radius of curvaturethat is larger than the initial radius prior to late flexion (e.g.,prior to about 90 degrees of flexion).

For example, in one embodiment shown in FIG. 19, the condyle surface 100be formed from a number of curved surface sections 700, 702, 704, thesagittal ends of each of which are tangent to adjacent curved surfacesections. The curved surface section 700 extends from an earlier degreeof flexion θ1 to a later degree of flexion θ2. The curved surfacesection 72 extends from the degree of flexion θ2 to a later degree offlexion θ3. The curved surface section 704 extends from the degree offlexion θ3 to a later degree of flexion θ4.

Each of the curved surface sections 700, 702, 704 is defined by arespective radius of curvature. In particular, the curved surfacesection 700 is defined by a radius of curvature R1, the curved surfacesection 6702 is defined by a radius of curvature R2, and the curvedsurface section 704 is defined by a radius of curvature R3. The radiusof curvature R2 is greater than the radius of curvature R1. The radiusof curvature R3 is less than the radius of curvature R2 and greater thanthe radius of curvature R1. In this way, the radius of curvature of thecondyle surface 100 initially increases from R1 to R2 and subsequentlydecreases to R3. However, because R3 is still greater than the distalradius R1, paradoxical anterior translation of the femoral component 12may be reduced or delayed as discussed in detail above.

Additionally, as discussed above, the particular amount of increasebetween R1 and R2 and between R1 and R3 may vary between embodiments andbe based on one or more of a number of various criteria such as, forexample, the type of orthopaedic prosthesis (e.g., cruciate retaining orposterior stabilized), positioning of other component of the orthopaedicprosthesis (e.g., the positioning of a cam of the femoral component 12),the size of the femoral cam, the curvature of the tibial bearing 14, theanatomy of a patient, etc. In one particular embodiment, each of theradius of curvature R2, R3 is greater than the radius of curvature R1 byat least 0.5 millimeters.

Referring now to FIG. 20, another way to control the radius of curvatureof the condyle surface 100 is to maintain the radius of curvaturethrough early to middle degrees of flexion. As discussed above, typicalfemoral components have decreasing radii of curvatures beginning at thedistal radius of curvature (i.e., at about 0 degrees of flexion).However, it has been determined that maintaining a relatively constantradius of curvature (i.e., not decreasing the radius of curvature) overa predetermined range of degrees of early to mid-flexion may reduce ordelay paradoxical anterior translation of the femoral component 12.

Accordingly, in one embodiment as shown in FIG. 20, the condyle surface100 may be formed from a curved surface section 800. The curved surfacesection 800 extends from an earlier degree of flexion θ1 to a laterdegree of flexion θ2. The curved surface section 800 is defined by aconstant or substantially constant radius of curvature R1. In theillustrative embodiment, the curved surface section 800 subtends anangle of about 110 degrees, but may be larger or small in otherembodiments. For example, in one particular embodiment, the curvedsurface section 800 subtends an angle of at least 50 degrees.Additionally, as discussed above, the particular degrees of flexion θ1,02 may be based on one or more of a number of various criteria such as,for example, the type of orthopaedic prosthesis (e.g., cruciateretaining or posterior stabilized), positioning of other component ofthe orthopaedic prosthesis (e.g., the positioning of a cam of thefemoral component 12), the size of the femoral cam, the curvature of thetibial bearing 14, the anatomy of a patient, etc.

The overall shape and design of the condyle surface 100 of the femoralcomponent 12 has been described above in regard to a single condyle 52,54 of the femoral component 12. It should be appreciated that in someembodiments both condyles 52, 54 of the femoral component 12 may besymmetrical and have similar condyle surfaces 100. However, in otherembodiments, the condyles 52, 54 of the femoral component 12 mayasymmetrical. For example, as illustrated in FIG. 21, the femoralcomponent 12 may include a second condyle 52, 54 having a condylesurface 900, which is defined in part by a plurality of curved surfacesections 902, 904. The curved surface section 902 extends from anearlier degree of flexion θ4 to a later degree of flexion θ5. The curvedsurface section 904 extends from the degree of flexion θ5 to a laterdegree of flexion θ6. The curved surface section 902 is defined by aradius of curvature R3 and the curved surface section 904 is defined bya radius of curvature R4.

As such, in embodiments wherein the condyles 52, 54 are symmetrical, thedegree of flexion θ4 is substantially equal to the degree of flexion θ1,the degree of flexion θ5 is substantially equal to the degree of flexionθ2, and the degree of flexion θ6 is substantially equal to the degree offlexion θ3. Additionally, the radius of curvature R3 is substantiallyequal to the radius of curvature R1 and the radius of curvature R4 issubstantially equal to the radius of curvature R2.

However, in other embodiments, the condyles 52, 54 are asymmetrical. Assuch, the degree of flexion θ4 may be different from the degree offlexion θ1. Additionally or alternatively, the degree of flexion θ5 maybe different from the degree of flexion θ2. That is, the increase inradius of curvature from R1 to R2 and from R3 to R4 may occur atdifferent degrees of flexion between the condyles 52, 54. Further, thedegree of flexion θ6 may be different from the degree of flexion θ3.Additionally, in those embodiments wherein the condyles 52, 54 areasymmetrical, the radius of curvature R3 may be different from theradius of curvature R1 and/or the radius of curvature R4 may bedifferent from the radius of curvature R2.

While the disclosure has been illustrated and described in detail in thedrawings and foregoing description, such an illustration and descriptionis to be considered as exemplary and not restrictive in character, itbeing understood that only illustrative embodiments have been shown anddescribed and that all changes and modifications that come within thespirit of the disclosure are desired to be protected.

There are a plurality of advantages of the present disclosure arisingfrom the various features of the devices and assemblies describedherein. It will be noted that alternative embodiments of the devices andassemblies of the present disclosure may not include all of the featuresdescribed yet still benefit from at least some of the advantages of suchfeatures. Those of ordinary skill in the art may readily devise theirown implementations of the devices and assemblies that incorporate oneor more of the features of the present invention and fall within thespirit and scope of the present disclosure as defined by the appendedclaims.

1. An orthopaedic knee prosthesis comprising: a femoral component havinga condyle surface curved in the sagittal plane; and a tibial bearinghaving a bearing surface configured to articulate with the condylesurface of the femoral component, wherein the condyle surface (i)contacts the bearing surface at a first contact point on the condylesurface at a first degree of flexion equal to about 0 degrees and (ii)contacts the bearing surface at a second contact point on the condylesurface at a second degree of flexion, the second degree of flexionbeing greater than the first degree of flexion, wherein (i) the condylesurface in the sagittal plane has a first radius of curvature at thefirst contact point and a second radius of curvature at the secondcontact point, and (ii) the second radius of curvature is greater thanthe first radius of curvature by at least 0.5 millimeters.
 2. Theorthopaedic knee prosthesis of claim 1, wherein the second degree offlexion is at least 10 degrees.
 3. The orthopaedic knee prosthesis ofclaim 2, wherein the second degree of flexion is in the range of 10degrees to 100 degrees.
 4. The orthopaedic knee prosthesis of claim 3,wherein the second degree of flexion is about 30 degrees.
 5. Theorthopaedic knee prosthesis of claim 1, wherein the second radius isgreater than the first radius by a distance of at least 2 millimeters.6. The orthopaedic knee prosthesis of claim 5, wherein the second radiusof curvature is greater than the first radius of curvature by a distanceof at least 5 millimeters.
 7. The orthopaedic knee prosthesis of claim1, wherein the ratio of the first radius of curvature to the secondradius of curvature is in the range of 0.50 to 0.99.
 8. The orthopaedicknee prosthesis of claim 7, wherein the ratio of the first radius ofcurvature to the second radius of curvature is in the range of 0.90 to0.99.
 9. The orthopaedic knee prosthesis of claim 1, wherein the condylesurface contacts the bearing surface at a third contact point on thecondyle surface at a third degree of flexion, the third degree offlexion being greater than the second degree of flexion and less thanabout 90 degrees, wherein (i) the condyle surface in the sagittal planehas a third radius of curvature at the third contact point and (ii) thethird radius of curvature is greater than first radius of curvature andless than the second radius of curvature.
 10. The orthopaedic kneeprosthesis of claim 9, wherein the third radius is greater than thesecond radius by at least 0.5 millimeters.
 11. The orthopaedic kneeprosthesis of claim 1, wherein the condyle surface contacts the bearingsurface at a third contact point on the condyle surface at a thirddegree of flexion, the third degree of flexion being greater than thesecond degree of flexion and less than about 90 degrees, wherein (i) thecondyle surface in the sagittal plane has a third radius of curvature atthe third contact point and (ii) the third radius of curvature isgreater than the second radius of curvature.
 12. The orthopaedic kneeprosthesis of claim 1, wherein: (i) the condyle surface of the femoralcomponent is a medial condyle surface and the bearing surface of thetibial bearing is a medial bearing surface, (ii) the femoral componentfurther includes a lateral condyle surface curved in the sagittal plane,and (iii) the tibial bearing further includes a lateral bearing surfaceconfigured to articulate with the lateral condyle surface of the femoralcomponent.
 13. The orthopaedic knee prosthesis of claim 12, wherein thelateral condyle surface and the medial condyle surface are substantiallysymmetrical in the sagittal plane.
 14. The orthopaedic knee prosthesisof claim 12, wherein the lateral condyle surface (i) contacts thelateral bearing surface at a first point on the lateral condyle surfaceat a third degree of flexion, the third degree of flexion being lessthan about 30 degrees, and (ii) contacts the lateral bearing surface ata second point on the lateral condyle surface at a fourth degree offlexion, the fourth degree of flexion being greater than the thirddegree of flexion, and wherein (i) the lateral condyle surface in thesagittal plane has a first radius of curvature at the first contactpoint, (ii) the lateral condyle surface in the sagittal plane has asecond radius of curvature at the second contact point, and (iii) thesecond radius of curvature is greater than the first radius of curvatureby at least 0.5 millimeters.
 15. The orthopaedic knee prosthesis ofclaim 14, wherein the second radius of curvature of the lateral condyleis different from the second radius of curvature of the medial condyle.16. The orthopaedic knee prosthesis of claim 14, wherein the seconddegree of flexion is different from the fourth degree of flexion. 17.The orthopaedic knee prosthesis of claim 14, wherein the differencebetween the first radius of curvature and the second radius of curvatureis different from the difference between the third radius of curvatureand the fourth radius of curvature.
 18. An orthopaedic knee prosthesiscomprising: a femoral component having a condyle surface curved in thesagittal plane; and a tibial bearing having a bearing surface configuredto articulate with the condyle surface of the femoral component, whereinthe condyle surface (i) contacts the bearing surface at a first contactpoint on the condyle surface at a first degree of flexion, the firstdegree of flexion being less than 30 degrees, and (ii) contacts thebearing surface at a second contact point on the condyle surface at asecond degree of flexion, the second degree of flexion being greaterthan about 30 degrees, wherein (i) the condyle surface in the sagittalplane has a first radius of curvature at the first contact point, (ii)the condyle surface in the sagittal plane has a second radius ofcurvature at the second contact point, and (iii) the ratio of the firstradius of curvature to the second radius of curvature is in the range of0.80 to 0.99.
 19. The orthopaedic knee prosthesis of claim 18, whereinthe ratio of the first radius of curvature to the second radius ofcurvature is from 0.90 to 0.99.
 20. An orthopaedic knee prosthesiscomprising: a femoral component having a condyle surface curved in thesagittal plane; and a tibial bearing having a bearing surface configuredto articulate with the condyle surface of the femoral component, whereinthe condyle surface (i) contacts the bearing surface at a first contactpoint on the condyle surface at a first degree of flexion, the firstdegree of flexion being about 0 degrees, and (ii) contacts the bearingsurface at a second contact point on the condyle surface at a seconddegree of flexion, the second degree of flexion being greater than about50 degrees, wherein (i) the condyle surface in the sagittal planeincludes a curved surface section extending from the first contact pointto the second contact point, the curved surface section being defined bya substantially constant radius of curvature.